NZ267045A

NZ267045A - Multiple capillary optical analyser

Info

Publication number: NZ267045A
Application number: NZ267045A
Authority: NZ
Inventors: Norman J Dovichi; Jian Zhong Zhang
Original assignee: Univ Alberta
Priority date: 1993-06-03
Filing date: 1994-06-02
Publication date: 1997-10-24
Also published as: AU695154B2; WO1994029712A1; AU6922394A; EP0701694B1; CA2164207A1; DK0701694T3; US5584982A; ES2106545T3; US5741412A; DE69405233T2; US5439578A; EP0701694A1; ATE157452T1; DE69405233D1

Abstract

A multiple capillary analyzer allows detection of light from multiple capillaries with a reduced number of interfaces through which light must pass in detecting light emitted from a sample being analyzed, using a modified sheath flow cuvette. A linear or rectangular array of capillaries is introduced into a rectangular flow chamber. Sheath fluid draws individual sample streams through the cuvette. The capillaries are closely and evenly spaced and held by a transparent retainer in a fixed position in relation to an optical detection system. Collimated sample excitation radiation is applied simultaneously across the ends of the capillaries in the retainer. Light emitted from the excited sample is detected by the optical detection system. The retainer is provided by a transparent chamber having inward slanting end walls. The capillaries are wedged into the chamber. One sideways dimension of the chamber is equal to the diameter of the capillaries and one end to end dimension varies from, at the top of the chamber, slightly greater than the sum of the diameters of the capillaries to, at the bottom of the chamber, slightly smaller than the sum of the diameters of the capillaries. The optical system utilizes optic fibres to deliver light to individual photodetectors, one for each capillary tube. A filter or wavelength division demultiplexer may be used for isolating fluorescence at particular bands.

Description

<div class="application article clearfix" id="description"> New Zealand No. 267045 International No. PCT/CA94/00304 TO BE ENTERED AFTER ACCEPTANCE AND PUBLICATION Priority dates: 03.06.1993; Complete Specification Filed: 02.06.1994 Classification:^) G01N21/01,64,85; G01N27/447; G01N35/08 Publication date: 24 October 1997 Journal No.: 1421 NEW ZEALAND PATENTS ACT 1953 COMPLETE SPECIFICATION Title of Invention: Multiple capillary biochemical analyzer Name, address and nationality of applicant(s) as in international application form: UNIVERSITY OF ALBERTA, Intellectual Property & Contract Office, 1-3 University Hall, Edmonton, Alberta T6G 2J9, Canada WO 94/29712 ^^ZboO 4 5 Title: MULTIPLE CAPILLARY BIOCHEMICAL ANALYZER FIELD OF THE INVENTION 10 This invention relates to apparatus used for biochemical analysis. BACKGROUND AND SUMMARY OF THE INVENTION Simultaneous analysis of a large number of 15 biological samples is useful in flow cytometry, DNA sequencing, liquid chromatography, oligonucleotide analysis, zone electrophoresis of proteins, as well as other electrophoretic techniques. In particular, rapid DNA analysis is of importance in the Human Genome Project, 20 which is an attempt to identify the sequence of bases (dideoxynucleotides) in human DNA. One technique that has been applied to the sequencing of DNA is capillary electrophoresis. In capillary electrophoresis, an appropriate solution is 25 polymerized or gelled to form a porous matrix in a fused silica capillary tube of internal dimensions in the order of 50nm. An electric field is applied across the matrix. Fragments of sample DNA injected into one end of the capillary tube migrate through the matrix under the effect 30 of the electric field at speeds that depend on the length of the fragment. Hence, different length fragments arrive at a detection part of the capillary at different times. The dideoxynucleotide at one end of the fragment may be labelled with a fluorescent marker during a reaction step. 35 The fluorescent marker is associated with the terminating dideoxynucleotide. When the fragment passes through a beam of light from a laser in the detection zone, the fluorescent marker SUBSTITUTE SHEET WO 94/29712 PCT/CA94/00304 fluoresces and the fluorescence may be detected as an electric signal. The intensity of the electric signal depends on the amount of fluorescent marker present in the matrix in the detection zone. The 5 dideoxynucleotide at the end of the fragment may then be identified by a variety of methods. As different length fragments migrate through the matrix under the applied field, a profile of the fragments may be obtained. 10 The use of three different DNA sequencing techniques is set out in Swerdlow, H. et al, Three DNA Sequencing Methods Using Capillary Gel Electrophoresis and Laser Induced Fluorescence. Anal. Chem., 53, 2P35-2841, Dec. 15, 1991, and the 15 references cited therein. In the Tabor and Richardson technique (one spectral channel sequencing), a single fluorescent marker is used, and the amount of dideoxynucleotide in the reaction mixture is varied so that each base of the DNA 20 fragment may be identified with a particular fluorescent peak height. For example, the concentration of dideoxynucleotides might be varied in the ratio of 8:4:2:1. The variation in fluorescence intensity with time will then identify 25 the sequence of bases. In the DuPont system (two spectral channel sequencing), succinylfluorescein dyes are used to label four dideoxynucleotides. A single wavelength (488nm) is used to excite fluorescence from the dyes. Emission is distributed 30 between two spectral channels centered at 510 and 540 nm. The ratio of the fluorescent intensity in the two spectral channels is used to identify the terminating dideoxynucleotide. In the Applied Biosystems system (four spectral channel 35 sequencing), four dyes (FAM, JOE, TAMRA and ROX) are used to label primers to be used with each WO 94/29712 PCT/C A94/00304 dideoxynucleotide reaction. Two lines from an argon laser (514.5 and 488 nm) are used to excite fluorescence. Interference filters are used to isolate emission at 540, 560, 580 and 610 nm and 5 peaks of the resulting four electrical signal profiles are used to identify the bases. Application of capillary electrophoresis to DNA analysis is complicated by the scattering of light from the porous matrix and the capillary 10 walls. For this reason, there has been proposed use of a sheath flow cuvette in which a sample stream of DNA is injected under laminar flow conditions in the center of a surrounding sheath stream, generally of the same refractive index. Such a cuvette is 15 described in Swerdlow H., et al, Capillary Gel Electrophoresis for DNA Sequencing; Laser Induced fluorescence detection with the sheath flow cuvette. Journal of Chromatography, 516, 1990, 61-67. However, the above described methods of 20 DNA sequencing using capillary electrophoresis have used single capillaries and rapid DNA sequencing and other biological process requiring simultaneous analysis of sample streams require use of multiple capillary systems. 25 One such multiple capillary system is described in Huang et al, Capillary Array Electrophoresis Using Laser Excited Confocal Fluorescence Detection. Anal. Chem. 64, 967-972, April 15, 1992. In the Huang device, multiple 30 capillaries lying side by side in a flat array holder are sequentially scanned by a laser beam and fluorescence detected from the capillaries using a photomultiplier tube. Such a device suffers from the same difficulties as with a single capillary that is 35 scanned with a laser, namely that there is light WO 94/29712 PCT/CA94/00304 scatter from the capillary walls and interfaces between the matrix and capillary. The inventors have therefore proposed a multiple capillary analyzer that allows detection of 5 light from multiple capillaries with a reduced number of interfaces through which light must pass in detecting light emitted from a sample being analyzed. In one aspect of the invention, there is 10 provided an analyzer for analyzing organic samples, the analyzer comprising: —'-.(a) ■ a flow chamber having an interior cavity and a detection region in said cavity,/ (b) means for introducing a sheath fluid into 15 said flow chamber and for flowing qZ said sheath fluid through said detection region, / (c) a plurality of capillary tubes extending into said chamber and/ having ends 20 terminating in said flow^chamber upstream of said detection region in the direction of sheath fluid iflow, for delivering samples to be/ analyzed into said detection regiem, 25 (d) means for /causing samples in said capillary / tubes to move from said capillary ends into said flow chamber so that sfaid samples are entrained as sample streams in said sheath fluid in said 30 detection region, means for removing said sheath fluid and said entrained sample streams from said detection region, and detection means for detecting samples 35 y in said ontrainod streams. (e). (f) 267045 a flow chamber (26) having an interior cavity and a detection region in said cavity, means (90) for introducing a sheath fluid (96) into said flow chamber (26)/ a plurality of capillary tubes (14) for receiving samples to be analyzed, and means (30) for causing samples in said capillary tubes (14) to move therein, characterized in that said means (90) for introducing said sheath fluid (96) causes aaid sheath fluid (96) to flow through said detection region as a common sheath fluid stream, said capillary tubes (14) having ends (18) terminating in said flow chamber (26) upstream of said detection region in the direction of sheath fluid flow, for delivering samples to be analyzed into said detection region, and said means (30) for causing said samples to move in said capillary tubes (14) causes said samples to move from said capillary ends (18) into said flow chamber (26) so that said samples are entrained as sample streams (58) in said common stream of sheath fluid (96) in said detection region, there being means for collecting said entrained sample streams (56) and said sheath fluid (96) as a common combined stream and including a port (108) downstream of said detection region for removing said common combined stream from said chamber, and detection means (36, 38, 40, 42, 44, 46, 48, 50, 52, 54, 56 or 36, 136, 137, 138, 140 or 142) for detecting samples in said entrained streams (58). In a further aspect of the invention, the capillary tubes form a two dimensional array, such array comprising plural rows of capillary tubes, each row of capillary tubes terminating at a different level from any other row of capillary tubes. In a still further aspect of the invention, the means for removing comprises a region in said chamber downstream of said detection region for collecting said sample streams and said sheath fluid as a common stream, and a port for removing said common stream from said amended sheet 26704! chamber, and wherein said capillary tubes have inlet ends for receiving sample, said capillary tubes containing an electrophoretic gel, said means for causing sample migration including means for applying an electrophoretic 5 voltage between said inlet ends and said first mentioned ends, said means for applying said voltage including means for grounding said sheath fluid. In a still further aspect, the invention provides a method of detecting substances in organic samples, 10 comprising! directing said samples through a plurality of capillary tubes (14) arranged side by side, said capillary tubes having ends (18), characterized in that a sheath fluid (96) is flowed as a common sheath fluid stream past said ends (18) of said capillary tubes (14) and said 15 samples are directed out of said capillary tubes (14) into said common sheath fluid stream so that said samples axe entrained as streams (58) in said common sheath fluid stream, detecting, said substances in said entrained sample streams (58), and after said detection, collecting said 20 entrained sample streams (58) and said sheath fluid stream (96) as a common combined stream and removing said common combined stream. WO 94/29712 PCT/C A94/00304 BRIEF DESCRIPTION OF THE DRAWINGS There will now be described a preferred embodiment of the invention, with reference to the drawings, by way of illustration, in which like 5 numerals denote like elements and in which: Figure 1 is an isometric schematic view of an exemplary biochemical analyzer according to the invention showing a sheath flow cuvette, multiple capillaries, a flow chamber and optical system; 10 Figure 2 is a section through the analyzer of Figure 1 without optical components; Figure 3A is a section through the chamber of Figure 1 showing the passage of a laser beam through the chamber; 15 Figure 3B is a schematic showing a light collection and detection system for used with the analyzer of Figure 2; Figure 4 is a section through the multi-capillary sheath flow cuvette of Figure 2 (the 20 section is through the center but also shows pedestals, which are off center, and appear behind the chamber): Figure 5 is a section at right angles to the section of Figure 4 (the section is through the 25 center but also shows pedestals, which are off center, and appear behind the chamber); Figure 6 is a section along the line 6-6 in Figure 5 showing the inlet for sheath fluid; Figure 7 is a section along the line 7-7 30 in Figure 5 showing the off center pedestals that retain the flow chamber; Figure 8 is a section along the line 8-8 in Figure 4 showing the base of the cuvette; Figure 9 is a section along the line 9-9 35 in Figure 4 showing a split rod with a slot along its central axis for retaining the capillary tubes; WO 94/29712 PCT/CA94/00304 Figure 10A is section through the top of the sheath flow cuvette; Figure 10B is longitudinal section through the sheath flow cuvette; 5 Figure IOC is a section through the bottom of the sheath flow cuvette; Figures 11A, 11B and 11C are graphs showing the results of DNA sequencing using apparatus according to the invention; 10 Figure 12 shows a schematic of a further method of detecting analyte; Figure 13 shows an apparatus for use for the electrochemical detection of analyte; Figure 14 is a schematic section of an 15 analyzer having a rectangular (in this case square) array in a square flow chamber; Figure 15 is a schematic view from the bottom of the chamber of Figure 14; and Figure 16 is an isometric view of a square 20 grid of capillaries for insertion in the chamber of Figure 14. DETAILED DESCRIPTION OF PREFERRED EMBODIMENTS Referring to Figures 1 and 2, there is 25 shown an analyzer for analyzing a sample of DNA including a sheath flow cuvette 12 enclosing the ends of five capillary tubes 14 arrayed side by side in a line like the teeth of a comb. The capillary tubes 14 are held in a header 16 with their cleaved 30 ends 18 terminating inside the chamber 12. The other ends 20 of the capillary tubes 14 terminate in five of the wells 22 of a conventional microtiter plate 24. The capillary tubes 14 are conventional fused silica capillaries, with about 50jim ID and 150nm OD, 35 available from Polymicro. The cuvette 12 is formed of a quartz chamber 26 secured within a stainless WO 94/29712 PCT/CA94/00304 8 steel holder 28, the design of which is shown in Figures 4 - 9 in more detail. A high voltage source 30, such as a Spellman RHR-30PN60 30 KV power supply, is connected to the stainless steel holder 5 28 through a first electrode 32 (grounded) and also through five second electrodes 34 to fluid in the wells 22. Thus, when the capillary tubes 14 and chamber 12 are filled with conducting material, a high voltage may be applied across the material in 10 the capillary tubes using the high voltage source 30. The circuit is formed by the grounded electrode 32, the stainless steel holder 28 (formed of cap 68, capillary retainer 64, chamber retainer 66 and cap 70), fluid in the cuvette 12 and in the chamber 26, 15 matrix in the* capillary tubes, including sample buffer if present, buffer solution in the wells 22 and the electrodes 34. A laser 36 or other source of collimated electromagnetic radiation provides a collimated beam 20 38 of light that is aligned to pass through a focusing lens 40 into the chamber 12 along a projection of the capillary tubes into the chamber, as close as possible to the ends of the capillary tubes 14, as shown in Figure 3A. The wavelength of 25 the laser 36 is chosen to excite fluorescence in the sample being analyzed, as for example DNA reacted with a fluorophor. An appropriate choice for DNA analysis is an Innova 70-4 argon ion laser available from Coherent Inc. of Palo Alto, California. Such 30 a laser may be operated with multiple wavelength mirrors (488 and 514.5 nm), with appropriate selection of the wavelength depending on the method used for sequencing the DNA. Fluorescence from the sample in the 35 chamber 12 is detected through a collection lens 42 that images the fluorescence on to a plurality of 1 WO 94/29712 PCT/CA94/00304 mm aperture GRIN (gradient index) lenses 44 (available from Nipon Scientific Glass through Precision Cslls, Inc. of Farmingdale, NY) which are affixed to receiving ends 46 of fiber optics 48. 5 The fibre optics 48 may be secured in known manner as for example to a Melles Griot optical bread board (not shown). Transmitting ends 50 of the fiber optics 48 lead into avalanche photodiodes 52 or other individual photon detectors, one for each 10 capillary tube 14, and whose output is connected through an interface 54 to a computer 56. Exemplary photodiodes 48 are RCA (EG&G) C30902S photodiodes, powered by a PS310 Stanford Research System high voltage power supply, or model SPCM 100 photodiodes 15 available from*EG&G Canada Ltd.. Fluorescence is transmitted along the fiber optics 48 to the photodiodes 52 whose electrical output is proportional to the intensity of the fluorescence. Electrical signals output from the photodiodes 52 20 are passed through a data acquisition board 54 (such as may be obtained from National Instruments or from Data Translation, model DT2221-G) to a computer 56 such as a Macintosh II computer for processing according to known techniques. Such processing 25 includes filtering the signal to give a desired frequency response, and a second filter or phase lock loop to identify the position of the peak centers. For interface boards from National Instruments, it may be necessary to decrease 30 illumination intensity to avoid over saturation of the photon detectors. Alternatively, light collected in individual GRIN lenses 44 may be passed through a bundle of optical fibres and imaged onto or abutted against an array detector. However, CCD 35 cameras are not believed to be fast enough for high speed DNA sequencing. WO 94/29712 PCT/C A94/00304 10 As shown in Figures 3A and 3B, if the fluorescence emitted from the DNA sample has a spectrum centered on more than one wavelength of light, then a means of dividing the spectrum of the 5 received light may be used. Light from laser 36 passes through focusing optic 40 and passes through the sample streams 58. Fluorescence from the sample streams is collected by optic 42 and passed through a spectral filter 60 (for filtering scattered light) 10 to GRIN lenses 44 on the ends of fibre optics 48. Light in the fibre optics 48 is passed through wavelength division demultiplexers 62 where light from different spectral bands is separated into two sets 48a and 48b of fibre optics and two sets of 15 avalanche photodiodes 52a and 52b. The selection of the filter 60 and the optical system depends on the sequencing reaction to be performed. For a single codor sequencer, using the sequencing method of Richardson-Tabor, a single 20 spectral filter 60 with a bandwidth of 45 nm centered at 530 nm may be used to detect fluorescein labeled products. The filter should be selected to minimize background signals due to Raman and Raleigh scatter of the excitation beam 38. For the DuPont 25 sequencing system, two detection channels are required, one detector channel to image light in a band centered at 510 nm and the other to image light centered at 540 nm. Light collected from the collection optic is split into two paths using the 30 wavelength division demultiplexers 62, one path leading to one set of photon detectors 52a and the other leading to the other set of photon detectors 52b. Other methods of wavelength division demultiplexing may be used as for example rapidly 35 switching a filter wheel so that the light from the sample stream is time division demultiplexed. For WO 94/29712 PCT/CA94/00304 11 sequencing using the method developed by Applied Biosystems Inc. (see the Swerdlow article), four channels are required. As with the DuPont system, two detector systems are used, and a filter wheel 5 may be used as the spectral filter 60 to rotate two selected filters across the path of the light collected by the collection optic. By alternating the two filters in the two detection systems, a signal from four spectral channels may be generated. 10 The collection optic 42 should be selected to provide an image that is matched in size to the aperture of the GRIN lenses 44, such as may be provided by a flat field high numerical aperture microscope objective, for example as made by 15 Leitz/Wild (0.^0 NA achromat objective). With a sample stream diameter of 50 nm and a GRIN lens diameter of 1 mm, for example, the magnification should be about 2Ox, generating spots several millimeters apart. Since the light from the 20 collection optic tends to expand with a curved wavefront, the GRIN lenses should be arranged to have their collection faces perpendicular to radii of the wavefront. Referring to Figures 4-9, the chamber 26 25 is held in a stainless steel holder 28 to form a sheath flow cuvette. The holder 28 includes an upper section or capillary retainer 64 and a lower section or chamber retainer 66 each machined from individual pieces of steel rod. The retainers 64 and 66 are 30 threaded together at 65 (threads not shown). A top cap 68 is threaded onto the upper end of retainer 64. A bottom cap 70 is threaded onto the lower end of retainer 66. An upper seal 72 made of plastic forms a seal between the cap 68 and retainer 64. A 35 like seal (not shown) may be used to seal the cap 7 0 to the retainer 66. An O-ring (not shown) or other WO 94/29712 PCT/C A94/00304 12 suitable seal should be provided to ensure that the retainers 64, 66 are sealed together to prevent leakage at 65. The cap 68 has a central hole for receiving the capillary tubes 14. A plastic sleeve 5 74 into which the capillaries are threaded has epoxy applied to it to form a seal around the capillary tubes 14 as they enter the cap 68. The capillary retainer 64 includes a hollow bore lined with a plastic cylindrical and annular spacer 76. Filling 10 out the hollow bore of the retainer 64 are two facing semi-circular metal rods 78 each with a groove machined into their facing flat faces to form a rectangular slot 80. The slot 80 is dimensioned to receive the capillaries 14 snugly and hold them 15 against each other in a line. The chamber retainer 66 includes two circular sections 82 and 84 and a pedestal section 86 in which the metal of the rod has been machined away to form four pedestals 88 in which the chamber 20 26 is securely retained. Metal in the chamber retainer 66 is machined away in the pedestal section 86 to form cavities 89. Removal of the metal in this section 86 allows a microscope objective to be placed close to the chamber 26 (within a few 25 millimetres). Upper circular section 82 includes a sheath fluid inlet 90 and a bubble removal port 92. The sheath fluid inlet 90 is connected via Teflon1" tubing 94 (see Figure 2) to a source of sheath fluid 96 (not shown to scale). The bubble removal port 92 30 is connected by Teflon"" tubing 98 to a valve 100. The tubing 94 may include a three way valve 102 with waste line 104 for removing bubbles from the sheath fluid. In the chamber retainer 66, at the base of the chamber 26 is a plastic bottom plug 106 that 35 holds the chamber 26 in place. The cap 70 is provided with a waste outlet port 108 that is WO 94/29712 PCT / C A94/00304 13 connected to TeflontlB tubing 110 to a waste beaker 112. As shown in Figure 2, sheath fluid is provided through inlet 90. The sheath fluid .iters 5 the top of the chamber 26 and moves as a syphon flow under gravity from the top of the chamber to the bottom, past the ends 18 of the capillary tubes 14. The fluid should be provided in a steady, non-pulsed flow, and should be filtered and purified to avoid 10 any background signal passing due to particles passing through field of view of the collection optics. The fluid is chosen to have similar index of refraction as the fluid carrying the sample DNA to avoid reflection and refraction at interfaces 15 between fluids*of different indexes of refraction. The simplest way to achieve this is to use the same fluid for the sheath fluid as carries the sample DNA, as for example lxTBE. The volumetric flow of the sheath stream is low, in the order of less than 20 10mli/hr, which for the embodiment described is in the order of 4mm/s, though it may be as much as lOx less for some applications. The fluid is drained to waste after exiting the chamber 12 through port 108. The waste beaker 112 should be kept half-filled with 25 buffer. If the waste stream forms drops, the sample stream profile is distorted when the drop detaches. A periodic noise results from the periodic detachment of the drops. The beaker 112 preferably has a small hole drilled in it with a tube leading 30 to a larger beaker 114. The level of the first beaker 112 remains constant, so that the sheath flow velocity under conditions of syphon flow changes slowly. A constant syphon head may also assist in ensuring constant sheath flow rate. For the 35 apparatus described a 5 cm syphon head has been found adequate. Bubbles should not be present in WO 94/29712 PCT/CA94/00304 14 the sheath flow. These can be eliminated by visual inspection and eliminated using the three way valve 102 (by switching the fluid containing the bubble to waste). 5 Referring to Figures 10a, 10b and 10c, the chamber 26 includes end walls 122a, 122b, side walls 124a, 124b, top 126 and bottom 128. The walls need not be planar but may contain projections to align the capillaries. Each wall is 1 mm thick at the top 10 and made of high quality optical quartz, or such other inert material as is transparent to the selected electromagnetic radiation emitted by either the laser 36 or the sample passing out of the capillary tubes 14. The side walls 124a, 124b are 15 constant thicknfess from top to bottom, while the end walls each thicken inward towards the bottom by 50nm. The interior of 130 of the chamber 26 has the same dimension X laterally as the thickness of the capillary tube used (150^im in the exemplary 20 embodiment) and the dimension Y1 from end wall to end wall a little more (50 ^un more in the exemplary embodiment) than the sum of the thicknesses of the capillary tubes 14. The interior 132 at the bottom of the chamber has the same dimension X laterally as 25 the thickness of the capillaries used and the dimension Y2 from end wall to end wall a little less (50nm in the exemplary embodiment) than the sum of the thicknesses of the capillary tubes 14. The capillary tubes 14 should be snugly fit in the 30 interior of the chamber 26, with their ends terminating adjacent each other. It is preferable that the capillary tubes 14 be placed in the chamber 26 before they are filled with matrix material. Particularly if capillary tubes are re-35 used, the collection optics, including the GRIN lenses 44, will be fixed and the capillary tubes 14 WO 94/29712 PCT/CA94/00304 15 must be aligned with the collection optic so that fluorescence from the sample stream irradiated by the laser beam 38 is imaged onto the GRIN lenses 44. The capillary tubes 14 are first inserted through 5 the cap 68 and retainer 64 into the slot 80 formed by the two rods 78. The capillary tubes 14 may be loaded together or one by one. The capillary tubes 14 are inserted into the chamber 26 in this manner and pushed together into the chamber 26 until they 10 are firmly held in the chamber 26. With the chamber 26 of the dimensions stated, the capillary tubes 14 will terminate about half way through the chamber 26. The top of the chamber 26 thus encompasses the capillary tubes 14 with the capillary tubes 14 15 abutting the interior walls of the chamber at the ends near the center of the chamber and at the sides throughout the length of the capillary tubes within the chamber 26. Abutment of the capillary tubes against the interior walls of the chamber seals any 20 gaps between the capillary tubes at the center of the chamber 26. Unless such gaps are sealed, non-uniformities in the sheath flow can result which can affect the signal quality. The capillary tubes 14 are preferably cleaved at their ends using well 25 known techniques employed in the manufacture of fiber optics in order to obtain a smooth and flat end. The capillary tubes 14 will therefore extend into the interior of the chamber 26 an amount that is dependent on the rate of decrease of the end wall 30 to end wall dimension of the chamber, and will typically be 1 cm for the exemplary embodiment described. The chamber 26 has height H about 2 cm from top to bottom as shown in the example. Such chambers may be purchased from Nipon Scientific 35 Glass through Precision Cells, Inc. of Farmingdale, NY, to order. The height H of the chamber is WO 94/29712 PCT/CA94/00304 16 somewhat arbitrary, sufficient to allow both fixture of the capillary tubes and to allow the light beam to pass through the chamber below the capillary ends. 2 cm is chosen to allow addition of a second 5 laser beam below the first if two lasers are used for analysis. The top of the side walls 124a, 124b should be slightly bevelled to ease insertion of the capillary tubes 14. The construction of the chamber is quite important, particularly when the capillary 10 tubes are not electrically isolated from the high voltage applied across the porous matrix material in the capillary tubes. If the capillary tubes are not isolated electrically, repulsive forces between them can create forces which if not evenly distributed, 15 can shatter the? capillary tubes. The capillary tubes 14 should therefore all be held securely in the chamber to prevent these stresses from concentrating at one tube. The capillary tubes 14 should terminate 20 within about lOjim from each other. The laser beam 38 should entirely pass within about 100 |im from the ends of the capillary tubes. Careful alignment of the capillary tubes is required so that the image of the fluorescence falls directly on the GRIN lenses. 25 This can be checked by passing light backward through the GRIN lenses. The light should pass through the sample stream exactly at the same point that fluorescence due to the laser beam occurs. Visual inspection can be used to verify the correct 30 alignment of the capillary tubes, with appropriate safety precautions due to the use of laser light. The length of the flow cell (distance between the end walls 124a and 124b) and the number of capillaries that can be detected ii^ a single flow 35 cell are determined by the distance over which laser beam size can be matched to the sample stream radius WO 94/29712 PCT/CA94/00304 17 as it exits the capillary. To optimize sensitivity, the laser beam should be located as near as possible to the ends of the capillaries to minimize effects of diffusion of the sample into the sheath fluid. 5 The laser beam should therefore pass through the acceleration region of the sample flow. At this point, faster moving sheath fluid draws the sample fluid from the matrix. Since the entire cuvette is grounded (through electrode 32), there is very 10 little electric field inside the cuvette, and the sample fluid is not drawn by the electric field out of the capillaries. Thus it is the sheath flow that draws the sample fluid from the matrix in the capillaries. As the sample fluid moves away from the 15 end of the capillary its cross-section contracts, and then expands due to diffusion of the sample fluid into the sheath fluid. The laser beam should pass through a point above the point of maximum contraction, thus before the diffusion zone. 20 A single laser beam is aligned to be parallel with the long axis of the cuvette (end wall 122a to end wall 122b) simultaneously exciting fluorescence from each sample stream in turn. The size of the laser beam should be selected to ensure 25 similar illumination of each sample stream. With a lens (for example a microscope objective with lx magnification) between the laser 36 and the chamber 26 a beam waist can be located in the center of the chamber. The beam spot size at the center of the 30 chamber should be equal to the sample stream diameter at that point. With 50 p ID capillary tubes, this is about 50 nm. The beam diameter will be larger in both directions away from this point, but with this arrangement, the fluorescence is close 35 to optimum. WO 94/29712 PCT/C A94/00304 18 For setting up the analyzer for DNA analysis, care must be taken as is known for capillary electrophoresis. Thus, the matrix material must be selected for stability, for discrimination 5 of longer base lengths and for speed of sequencing. No one matrix is suitable for all applications. For DNA sequencing, a 0%C (non-cross-linked), 5-6%T acrylamide gel has found to be adequate and has the added advantage of low viscosity which allows it to 10 be readily replaced, without removal of the capillary tubes 14 from the chamber 26. A proprietary gel, Long-Rangertn from AT Biochemicals, has been found useful for applications using high voltage in the order of 800V/cm, such as in 15 diagnostic applications. Long-RangertBI gel allows sequencing rates in the order of 200 bases in 3 minutes with greater than 95% accuracy. 0%C gels provide sequencing rates in the order of 600 bases in two hours at 200V/cm. Gel temperatures between 20 20°C and 35°C have been found to give good results. The Long-Ranger gel is prepared within a 50 jim ID capillary by polymerization of a carefully degassed 5% solution of Long-Ranger in a 7 M urea, 0.6 x TBE buffer. Polymerization is initiated with 25 0.4 parts per thousand (V/V) TEMED and o.4 parts per thousand (W/V) ammonium persulphate. Such a gel is stable and may be used for three separations. Use of Long-Ranger gel with a single 50|im ID capillary has yielded sequencing rates of 3200 bases per hour at 30 800V/cm. The gel may include 0 - 20% of formamide. Addition of formamide in this range decreases compressions, particularly in the range 10 - 20%, thereby increasing resolution in regions of 35 compression. However, it has been found that too much (20% or more) formamide reduces the separation WO 94/29712 PCT/C A94/00304 19 rate, theoretical plate count, and resolution for normally migrating fragments without a concomitant decrease in compressions. An optimum concentration of 10% formamide improves resolution of compressed 5 regions without degrading other characteristics of the gel. It has also been found that operating the gel at room temperature is adequate and simplifies the engineering of the analyzer. Results of using formamide have been described in Rocheleau, M.J., et 10 al, Electrophoresis, 13, 484-486, li'92. The gel should be established in the capillary tubes 14 without voids or bubbles forming during polymerization of the acrylamide due to shrinkage, which may be particularly acute if a 15 bifunctional silane reagent is used to bind the gel to the capillary wall. Such bubbles can be eliminated by use of low percent acrylamide, short columns, adding polyethylene glycol to the monomer mixture (though this is not desired for DNA 20 fragments longer than about 100 bases since it degrades the separation) or by allowing polymerization to occur in a pressured vessel or other methods known in the art. Also, defects in the gel at the ends 20 25 may occur when loading samples of DNA into the capillary tubes 14. Such defects are particularly of concern when the capillary tubes 14 are reused. It is therefore desirable to cut off a portion (several millimetres) of the capillary tube 14 after a run. 30 Also, such a defect can be minimized by loading smaller amounts of DNA sample, as much as five times lower, as compared with conventional electrophoresis sequencing of DNA. Thus for example the sample using the apparatus disclosed should be loaded at 150V/cm 35 for 60 s. WO 94/29712 PCT/CA94/00304 20 Flaws in the gel can be inspected by-visual inspection in a microscope or by passing two laser light beams at an angle through the gel to intersect each other in the gel. Modulated light 5 scatter of the laser light from flaws in the gel may be detected using a collection optic and photomultiplier tube. Loading of the gel into the capillary tubes 14 also requires care. It is desirable that 10 gel characteristics be uniform from capillary tube to capillary tube. If the capillary tubes are loaded with gel sequentially, differences in the gel may severely degrade the analysis. It is preferable to load the gel monomer into a single container and to 15 fill the capillaries with the gel from the single container simultaneously, as by vacuum syphoning the gel. At high electric fields (in the order of 800V/cm), the gel can extrude about 50 nm from the detection end of the capillary. To eliminate 20 extrusion, about 2 cm of the gel at the detection end is covalently bonded to the interior walls of the capillary tubes with y-methacryloxypropyltrimethoxysilance. Such known methods for establishing a gel as described in 25 United States patents 4,865,706 and 4,865,707 to Karger et al and 4,810,456 to Bente et al may also be used. Data has been collected from the system of Figure 1. with detection at three capillaries using 30 the Tabor and Richardson sequencing technique. An M13mpl8 template was used to generate fragments of DNA. Manganese was used instead of magnesium in the sequencing buffer. Sequenase was used for chain extension. A FAM labeled priiper is used and a single 35 sequencing reaction is performed with ddATP, ddCTP, ddGTP and ddTTP present in a 8:4:2:1 ratio. A 50nm WO 94/29712 PCT/CA94/00304 21 capillary was filled with 4%T, 5%C gel and operated at 200V/cm. For a run of 330 bases in 70 minutes, comparable data was obtained as for single capillary systems, although the throughput was 850 bases/hour 5 for a 3 capillary system. Figures 11a, lib and 11c show the results of the sequencing. Resolution is limited to fragments less than 300 bases in length at high voltages near 800V/cm. Generally speaking, retention time 10 increases linearly with fragment length for a given high V/cm until the mobility of the fragments approaches a limiting value and no separation is achieved. This is called biased reptation. As the electric field increases, the transition to biased 15 reptation moves to shorter fragments. Biased reptation is highly undesirable since it causes sequencing fragments to coelute, destroying the separation resolution. Hence for longer fragments (in the order of 600 bases), the electric field can 20 be decreased to about 140 V/cm, with an increase in separation time. Moderate gel temperature (in the order of 20° to 35°C) can assist in improving sequencing rate, though it does not appear to strongly affect the transition from reptation to 25 biased reptation. Lower %T acrylamide gels can also assist in the sequencing of longer fragments. The analyzer described here has utility for a wide variety of applications, with some modifications. In each case there is some means to 30 force analyte through the capillaries, the capillaries are held in the chamber as shown in Figure 1 and 2 for example, and sheath fluid is supplied through the cuvette, with the sheath fluid preferably having the same index of refraction as 35 the fluid carrying the analyte. WO 94/29712 PCT/C A94/00304 22 The detection of analyte may also be accomplished using thermooptical absorption. In this technique, the laser 36 is used to excite the analyte which tends to heat the analyte and change 5 the index of refraction of the fluid by which it is carried. As shown in Figure 12, the deflection of the beams 138 from a second laser 136 after collimating with an appropriate optic 137 by the sample fluid emerging from the ends of the capillary 10 tubes 14 is then detected by the optical system 140, which may be designed as shown in Figure 1. An analyzer for use as an electrochemical detector is shown in Figure 13. Electrodes 142 enter the chamber 26 (made of an inert non-conducting 15 material such as quartz) from the bottom end 132 of the chamber. Each electrode 142 is connected to an amplifier (not shown), and the output of the amplifier is provided to a processor, for example a computer, through an interface for analysis in 20 accordance with known principles (similar to the optical processing of the signals). In such a case, the laser 36 is not required, since the identification of the sample is by electrochemical analysis. Multiple capillaries allow for rapid 25 analysis. The analyzer may also be used to detect impurities in fluids by detecting light scatter. In such a case, the high voltage source 30 is not required, since the fluid may be pumped directly as 30 a fluid through the capillary tubes, nor is the spectral filter 60 required since the total intensity of the scattered light may be detected. The GRIN lenses 44 and detectors 52 detect variations in the scatter of light resulting from 35 particles or impurities in the fluid. WO 94/29712 PCT/CA94/00304 23 The analyzer is also useful for the detection of organic contaminants, for example the fluorescent detection of polycyclic aromatic hydrocarbons. In such detection, the capillary tubes 5 are filled with chromatographic packing material (coated silica beads) instead of a polymer and the analyte sample is forced through the capillary tubes using a pump instead of the high voltage source 30. The laser 36 should emit radiation at about 330 nm 10 or such other appropriate wavelength for detection of organic contaminants. Fluorescence emitted by the sample of contaminant is detected through an appropriate spectral filter 60 and the optical apparatus shown for example in Figure 1. 15 In a 'further example, the analyzer may be used for flow cytometry. In flow cytometry a sample containing cells taken from an animal or human body by fine needle aspiration is stained using a fluorescent reagent such as a nucleic acid stain or 20 antibodies. With the present analyzer, the sample is forced under air pressure by a pump that replaces the high voltage source 30 through the capillary tubes 26 and the laser beam 38 is passed through the sample as it emerges from the capillary tubes 26 25 into the sheath flow. The intensity of the fluorescence from the fluorescent reagent is detected using the optical system of Figure 1 and used to estimate the number of sets of chromosomes in the cells, and this is useful, in accordance with 30 known procedures in the diagnosis and prognosis of cancer. Multiple capillary tubes may also be used to spray analyte into a mass spectrometer. In such a case, the capillaries are bundled within a 35 circular or polyhedral cuvette with sheath flow about the capillaries. The bundle of capillaries is WO 94/29712 PCT/C A94/00304 24 inserted into the ionization chamber of a mass spectrometer such as the triple quadrupole mass spectrometer sold by Sciex Division of MDS Health Group Limited, of Thornhill, Ontario, Canada, under 5 its trademark TAGA 6000E. For electrospray of analyte, the capillary tubes are made conducting at the end that extends into the ionization chamber. Electrical potential is applied to the ends of the capillaries in known manner. 10 A square, rectangular or other suitable polyhedral array of capillary tubes may also be used as well, as shown in Figures 14, 15 and 16 for the case of a square capillary array. The array may be rectangular as well. Other polyhedral arrays could 15 be used in principal, but this complicates the optics. The array of capillary tubes 14 is formed from five rows 144 of five capillary tubes 14 each, all bound within a square chamber 146 forming part of a square sheath flow cuvette. The cuvette is 20 similar to the cuvette shown in Figures 4-9 only the central chamber is square. An optical system 148 disposed adjacent the cuvette includes a collection optic 154, GRIN lenses 156, and optic fibres 158 leading to photodiodes and the balance of the 25 optical system as shown in Figure 1. Each row 144 of capillary tubes is similar to the row shown in Figure 1, but succeeding rows in the direction of the optical system 148 terminate higher in the sheath flow cuvette as shown at 160. 30 All capillary tubes 14 in a row terminate adjacent each other. Sheath flow is provided about all of the tubes 14 within the sheath flow cuvette. All four walls 150 of the sheath flow cuvette taper inward towards the bottom 152 of the chamber. The ends of 35 the capillary tubes 14 define a sloping plane P, sloping downward and away from the optical system WO 94/29712 PCT/C A94/00304 25 148. An elliptical or other linear cross-section laser beam 162 oriented at the same slope as the sloping plane (or close to it) is directed just below the ends of the capillary tubes 14. 5 Fluorescence of the samples forms a sloping square array of fluorescent spots 164 that appears as a square grid of spots 166 from a view at right angles to the cuvette. Fluorescence from sample streams emerging 10 from the capillary tubes 14 is collected by an optic 154 and imaged on to the square array of GRIN lenses 156, which lie in the image plane of the fluorescent spots produced by the optic 154. The GRIN lenses 156 are oriented with their faces perpendicular to the 15 wavefront from* the collection optic 154. Light collected by the GRIN lenses is transmitted through optic fibres to photodetectors of the type shown in Figure 1. It is possible to operate the cuvette 20 upside down to allow bubbles in the sheath stream to move upward with the stream to waste. A person skilled in the art could make immaterial modifications to the invention described and claimed in this patent document without 25 departing from the essence of the invention. </div>

Claims

<div class="application article clearfix printTableText" id="claims"> I CLAIM» - 26 - 267 045

1. An analyzer for analyzing organic samples, the analyzer comprisingt a flow chamber having an interior cavity and a detection region in said cavity,

5 means for introducing a sheath fluid into said flow chamber , a plurality of capillary tubes for receiving samples to be analyzed, and means for causing samples in said capillary tubes to move therein, characterized in that said means for

10 introducing said sheath fluid causes said sheath fluid to flow through said detection region as a common sheath fluid stream, said capillary tubes having ends terminating in said flow chamber upstream of said detection region in the direction of 15 sheath fluid flow, for delivering samples to be analyzed into said detection region, and said means for causing said samples to move in said capillary tubes causes said samples to move from said capillary ends into said flow chamber so that said samples are

20 entrained as sample streams in said common stream of sheath fluid in said detection region, there being means for collecting Baid entrained sample streams and said sheath fluid , as a common combined stream and including a port downstream cf said detection region

25 for removing said common combined stream from said chamber, and detection means for detecting samples in said entrained streams.

2. Apparatus according to claim 1 wherein said 30 detection means comprises an electromagnetic radiation detector , characterized in that there are means for'

simultaneously applying electromagnetic radiation through said entrained streams.

35

3. Apparatus according to detection means claim 2 wherein

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AMENDED SHEET

2 0 fi33 1SS'

267045

- 27 -

are optical detection means

, characterized in that said means for simultaneously directing electromagnet radiation through said entrained streams comprises laser means.

5

4. Apparatus according to claim 3 characterized in that the ends of said capillary tubes are arranged in a straight line.

5. Apparatus according to claim 4 vherein said capillary tubes each have an interior passage and an

10 exterior surface/ characterized in that said interior passages are evenly spaced apart in said flow chamber.

6. Apparatus according to claim 5 characterized in that said exterior surfaces of said capillary tubes contact the exterior surfaces of adjacent capillary tubes

IS adjacent said ends of said capillary tubes.

7. Apparatus according to claim 1 characterized in that said capillary tubes • - • " form a two-dimensional array.

8. Apparatus according to claim 7 characterized in 20 that said two-dimensional array comprises plural rows of capillary tubes ~, each row of capillary tubes terminating at a different level from any other row of capillary tubes.

9. Apparatus according to claim 8 characterized in 25 that said array is a rectangular array.

10. Apparatus according to claim 9 characterized in that said exterior surfaces of said capillary tubes contact the exterior surfaces of adjacent capillary tubes adjacent said ends of said capillary tubes.

r " 3

amended sheet ' 1

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26 7 0 45

11. Apparatus according to any preceding claim wherein said capillary tubes contain an electrophoretic gel characterized in that said means for causing sample migration includes an electrophoretic 5 voltage source operable to cause samples within a capillary tube ' to migrate towards said ends of said capillary tubes.

12. Apparatus according to any one of claims 1 and 7 to

10 wherein said flow chamber includes a side wall

10 portion adjacent to said detection region,

characterized in that said side wall portion is transparent to electromagnetic radiation, said detection means including a source of collimated electromagnetic

IS radiation having a wavelength that may excite said sample to emit radiation and that is aligned to pass through said transparent side wall portion and to provide colligated light through the entrained streams of sample in said detection region.

20

13. Apparatus according to claim 1, 7 or 8

characterized in that said means to force sample through said capillary tubes ^ comprises a pump and the capillary tubes contain chromatographic packing material.

25

14. Apparatus according to claim 1, 7 or 8 wherein said chamber includes £?lr*fc and second opposed portions, characterized in that the means to Introduce sheath fluid . includes a tube ~ connected to said first portion of said chamber , the

30 second portion ''of said chamber encircling said ends of said capillaries.

15.

Apparatus according to any one of claims 1 to 10

characterized in that said chamber amended sheet has an encircling kj *J hX J tZ'jf

.a. 26704 5

aide wall which tapers inwardly from a separation that is greater than the sum of the capillary tube diameters to a separation that is less than the sum of said capillary tube diameters.

5

16. Apparatus according to any one of claims 1 and 7 to

10 in which said detection means is an optical detection system, characterized in that said detection system comprises a wavelength division demultiplexer for

10 separating radiation emitted from said entrained streams into light of at least two spectral bands, and means for detecting radiation for each of said spectral bands.

17. ApparttUB aeeafdias to hfiy one of claims 1 to 10, 15 characterized in that said chamber is held at ground potential.

18. Apparatus according to any one of claims 1 and 7 to 10 wherein said chamber is at least partially formed of a transparent material, characterized in that said

20 chamber includes a recessed portion adjacent said detection region wherein said transparent material of said chamber is exposed, said detection means

Including a source of collimated radiation i " and means 25 for receiving emitted radiation from said entrained sample streams, the source of collimated radiation " and means for receiving emitted radiation being positioned in said recessed portion and adjacent to said transparent material.

30

19. Apparatus according to any one of claims 1 to 10

wherein said organic material is carried in said capillaries by a fluid, characterized in that said fluid has essentially the same index of refraction as the

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- 30 -

sheath fluid.

26 7 04 5

20. Apparatus according to any one of claims 1 to 10

characterised in that there are means to prevent drop formation of fluid leaving said exit port.

5

21. Apparatus according to any one of claims 1 to 10 characterised in that there are means for preventing drop formation of fluid leaving said exit port

. , said means to prevent drop formation comprising a

10 container at least partially filled with sheath fluid >/ connected to said exit port and into which sheath fluid _ .' from said chamber drains.

22. Apparatus according to any one of claims 1 to 10 10 characterized in that said detection means

15 comprises a thermal-optical absorption detector.

23. Apparatus according to anyone of claims 1 to 10 wherein said organic samples are carried in said capillary tubes in a fluid, characterized in that said

20 detection means comprises: a first laser " aligned with said array of capillary tubes for simultaneously exciting the organic samples in said entrained sample streams and for heating said fluid, a second laser for passing a laser beam

25 through each of said entrained sample streams in a direction generally orthogonal to the direction of alignment of said first laser and an optical system for receiving emitted light from said entrained sample streams.

30

24. Apparatus according to any one of claims 1 and 7 to

10 characterized in that said detection means

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- 31 - 267 0 4 5

comprises an electrochemical detector.

25. Apparatus according to any one of claims 1 to 10

wherein said capillary tubes contain an electrophoretic gel, characterized in that said means for 5 causing sample migration includes means for applying an electrophoretic voltage between said inlet ends and said first mentioned ends , said means for applying said voltage including means for grounding said aheath fluid.

10

26. A method of detecting substances in organic samples, comprising! directing said samples through a plurality of capillary tubes arranged side by side,

said capillary tubes having ends , characterised in that a sheath fluid "" is flowed as a common sheath 15 fluid stream past said ends of said capillary tubes and said samples are directed out of said capillary tubes into said common sheath fluid stream so that said samples are entrained as streams ~ in said common sheath fluid stream, detecting said substances in said 20 entrained sample streams », and after said detection, collecting said entrained sample streams _ ' and said sheath fluid stream as a common combined stream and removing said common combined stream.

27. The method according to claim 26, characterized 25 by the step of directing a beam of collimated electromagnetic radiation through said entrained sample streams , and detecting radiation from said entrained sample streams.

28. The method according to claim 27 characterized 30 by the step of illuminating said entrained sample streams substantially simultaneously by electromagnetic radiation from a laser.

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amended sheet

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, 32 . 26 7 0 4 5

29. The method according to claim 28 characterized in that said capillary tubes are arranged in a two-dimensional array so that said entrained sample streams are arranged in a two-dimensional array in said 5 common sheath fluid stream, and illuminating all of said entrained sample streams substantially simultaneously with a beam of collimated electromagnetic radiation.

30. The method according to claim 29 characterized in that said two-dimensional array is formed o£ plural

10 rows * of capillary tubes ., each row terminating at a different level from any other row of capillary tubes , and wherein said step of detecting comprises detecting radiation from each of said entrained sample streams in a direction at right

15 angles to said beam.

31. The method according to any one of claims 26 to 30, characterized in that said sheatu fluid _ ' is maintained at ground potential.

32. The method according to any one of claims 26 to 30, 20 characterized by the step of holding the exterior surface of each capillary tube in contact with the exterior surfaces of adjacent capillary tubes ^ , adjacent said ends.

END OF CLAIMS

"V. ♦ .

amended sheet

</div>